Pliable medical device and method of use

ABSTRACT

A firm but pliable medical device for use as a bone graft substitute or bone graft extender retains its shape without the requirement of a containment device, such as a syringe. Because the device is solid, it is easy to locate or position in-vivo and, in the moist environment of the body, it will hold its shape well, for an extended time. Because the lyophilized pliable medical device is porous, it adsorbs blood and other beneficial cells containing body fluids, such as bone marrow, contributing to its superior bone repair efficacy in comparison to an analogous putty that has not been lyophilized. In addition these lyophilized pliable medical devices are easier to terminally steam sterilize than the analogous putty because there is no moisture present to boil and “blow-out” of the containment device (syringe). The glycerin that is present in the formulation lends pliability but has a low vapor pressure.

This application is being filed on 15 Dec. 2006, as a PCT International Patent application in the name of CeraPedics, L.L.C., a U.S. national corporation, applicant for the designation of all countries except the US, and James John Benedict, Greg Allen Brewster and Donald Barclay Freeman, citizens of the U.S., applicants for the designation of the US only, and claims priority to U.S. Utility patent application Ser. No. 11/305,715, filed Dec. 16, 2005.

FIELD OF THE INVENTION

This invention relates to the field of surgical repair of skeletal elements. More particularly, the invention is a method and composition for use as a bone graft substitute or bone graft extender for filling or otherwise repairing bone damage and promoting bone formation in mammals using a composition that is a firm but pliable medical device that will retain its shape without the requirement of a containment device, such as a syringe.

BACKGROUND OF THE INVENTION

Physicians are sometimes called upon to repair bone that has been damaged by disease, trauma, osseous surgery or other causes, or to cause bone material to grow where there has been no bone before, such as during a spine fusion procedure. As an outcome of that procedure, it is desirable for two or more vertebral bodies to be maintained in a specific orientation. This can be accomplished by growing a column or bridge of rigid bone between the vertebral bodies. This maintains them in a fixed position relative to each other. The repair of long bone fractures can often be accomplished merely by relocating disrupted bone elements into natural proximity and fixing them in place until they can heal together. This is the approach taken in repairing ordinary limb fractures, for example. The fractured bone is re-set, then immobilized for a period of weeks in a rigid or semi-rigid cast or splint as the fractured elements heal.

Sometimes, however, this approach is insufficient because the patient has lost some of the bone. This can happen in certain kinds of trauma where the bone is so badly shattered that it cannot feasibly be pieced together. More often, it happens as a result of disease that destroys bone mass or as the result of osseous surgery in which destruction of bone mass is unavoidable. In these cases, there is no “piece” of the patient's bone to re-set into proper position for healing. Instead, there is a void or defect that must somehow be filled, or a gap between two bone structures that needs to be filled with new bone. The filling of this defect or gap requires a material that is not only biocompatible but preferably will accept or even promote in-growing natural bone as the site heals. In such a manner, the material ideally will eventually become resorbed as new in-growing natural bone takes its place as part of the skeletal structure. Completely resorbed material eliminates the possibility for a stress riser that can occur when foreign matter remains in the skeleton, potentially giving rise to a fracture in the future.

Numerous bone replacement materials have been employed by physicians with varying degrees of success. One approach is to use bone material recovered from the patient himself, or so-called autologous bone. This approach is advantageous in that it avoids biocompatibility and bio-rejection problems. However, such an approach necessarily involves two surgical procedures, two surgical sites, and two healing processes—one for the original injury and a second for the site of the donated bone material. This means greater cost, and increased risk of infection and morbidity for a patient that is already seriously ill or injured. Also, this approach can require a great deal of time and surgical skill as the surgeon removes the donated material from the donation site, shapes and fits it to the primary site, and then repairs both sites. Finally, there is quite obviously a limit to the amount of bone in the patient's body available to be sacrificed as donor material.

Another approach uses human bone but not harvested from the patient. This is called allograft bone. Allograft bone is typically harvested from cadavers. It contains endogenous bone morphogenic proteins (“BMP”) and is available both in structurally intact and demineralized forms. Such material can become integrally incorporated into the patient's own skeletal system.

Demineralized allograft is routinely offered by commercial medical suppliers in dry granulated or powdered form of varying fineness. These dry granules or powder generally lack sufficient cohesiveness and adhesion for filling an osseous defect. Therefore, they are mixed with an appropriate carrier. The carrier in the past has sometimes been the patient's own blood or bone marrow. Such a carrier is of course plentiful at the surgical site, is biocompatible with the patient, and contains biological agents that promote new growth in the allograft bone elements suspended in it. On the other hand, using the patient's own blood necessitates a mixing step which might not be controlled precisely in the operating room to achieve the desired consistency. In addition, blood is not of the ideal consistency or viscosity for such an application.

Glycerol and other biocompatible materials have been used as alternate carriers in combination with demineralized allograft bone. Glycerol is suitable in consistency and viscosity for this application, but suffers from certain functional drawbacks. Because glycerol is water soluble, it could allow early dispersement of the suspended bone after being placed in the bone defect at the injury site.

Purified forms of human or animal derived collagen have been described previously for use in bone graft substitutes. When used by itself, in lyophilized form, collagen is not entirely suitable for use as a bone graft substitute. It resorbs too quickly to be an effective scaffold for bone accretion. In order for bone formation to occur, osteogenic cells (cells capable of producing bone) must attach to the osteoconductive substrate and begin the process of bone formation. The substrate must remain present long enough to allow bone formation to progress to the point of being self sustaining. Collagen can be chemically modified to make it less bioresorbable. Chemical cross linking agents such as formaldehyde and glutaraldehyde have been described. Unfortunately, low residual levels of these agents are cytotoxic and can affect bone formation in a negative manner.

Lyophilized collagen devices also compress, under soft tissue forces, not maintaining an adequate space for bone ingrowth to occur. In such circumstances, collagen can be used in combination with alloplast materials for maintaining an adequate “healing volume.” Even in these instances though, collagen still suffers the disadvantage of being a possible sensitizing agent in patients at risk for having an allergic response to collagen. In the case of bovine or other animal collagen, there is also a concern about the transmission of animal diseases, such as Bovine Spongiform Encephalopathy (BSE, or Mad Cow Disease) to the patient.

As a substitute for glycerol, high-molecular weight hydrogels, such as sodium hyaluronate, have been used to form a malleable bone putty which includes allograft bone powder suspended therein. Hyaluronon is a polysaccharide that occurs naturally in the body in the form of hyaluronic acid or in the salt form such as sodium hyaluronate. It is highly hydrophilic, viscous, and extremely lubricous. High-molecular weight hydrogels will allow suspension of very small particle sizes of allograft material.

However, even hydrogels may tend to disperse from the bone defect site. In addition, hydrogels are not conducive to retaining the body's own fluids or bone marrow aspirate which may be delivered to the defect site. There is therefore a need in the art for an improved bone graft substitute that overcomes these and other deficiencies.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 shows a picture of a cylinder shaped embodiment of the pliable medical device of the present invention and its flexibility.

FIG. 2 shows a picture of a cylinder shaped embodiment of the pliable medical device of the present invention being cut with scissors.

FIG. 3 shows a picture of a cylinder shaped embodiment of the pliable medical device of the present invention being placed into a bone defect.

FIG. 4 shows a picture of a sheet embodiment of the pliable medical device of the present invention and its flexibility.

FIG. 5 shows a picture of a cube shaped embodiment of the pliable medical device of the present invention being placed into a metal spine fusion cage.

FIG. 6 shows a picture of a cube shaped embodiment of the pliable medical device of the present invention being placed into a hollow central portion of a fibular ring allograft device.

DETAILED DESCRIPTION OF THE INVENTION

The nature of the present invention begins with the preparation of a hydrogel material. The following description is by way of example, and specific amounts of material listed may be varied substantially to achieve the same or similar results. Thus, the specific amounts shown below are by way of example only and are not intended to be limiting to the scope of the invention.

A mixing operation is performed in a stainless steel, one quart, Ross double planetary mixing unit fitted with a closure allowing for operation under partial vacuum. First, 31.5 grams of sodium carboxymethylcellulose (NaCMC) is completely dispersed in 145.3 grams of glycerin (USP). The dispersion is added in approximately equal amounts to each of three 60 ml disposable plastic Luer-lock fitted syringes. Alternative dispersing agents can be used. For example, in the formulations of the invention glycerin may be replaced by polyethylene glycols, N-methyl pyrrolidone, or triacetin.

With the mixing unit under partial vacuum (15 inches of mercury (Hg)) one of the NaCMC dispersion containing syringes is connected to the mixing unit via a Luer-lock fitted entry port and the contents of the syringe are added to the mixing unit. While mixing at a moderate speed (100 rpm) about 30% of a total of 823.2 grams of sterile water for injection (WFI) is added to the mixing unit. Next, the contents of a second NaCMC dispersion containing syringe is added to the mixing unit along with an additional 30% of the total WFI. Finally, contents from the third NaCMC dispersion containing syringe and all but about fifty ml of the remaining WFI is added to the mixing unit. The remainder of the WFI is used to rinse the syringe entry port. The vacuum in the mixing unit is adjusted to greater than twenty inches of Hg and the contents mixed at medium speed (150 rpm) for about thirty-five minutes. Then, the vacuum is broken and mixing discontinued. The resulting hydrogel material from the mixing unit is transferred to a closed storage container. The hydrogel material is allowed to hydrate at room temperature, about 25° C. for at least six hours. The process may be speeded up by placing the closed storage container in an environment with an elevated temperature, such as 40° C.

Next, about 240 grams of the hydrated hydrogel material is transferred to the mixing unit along with about 130 grams of anorganic bone mineral matrix (ABM), a calcium phosphate ceramic, which may be coated with a biologically active peptide. Several different biologically active peptides may be used. For example, P-15 is a peptide fragment taken from Type I collagen and acts as a cell binding agent. Chrysalin is a peptide fragment taken from the biomolecule thrombin. Chrysalin is reported to have effects on blood vessel formation. Cytomodulin is a bioactive 7 amino acid synthetic protein patterned after a peptide sequence found in the biomolecule TGF-beta. Cytomodulin is further described in U.S. Pat. No. 5,661,127. The alpha1(I)-CB3 fragment of type I collagen contains the reportedly biologically active fragment DGEA [J. Biol. Chem., 266(12) p-7363 (1991)] that bind the alpha2/beta1 integrin. Type I collagen also contains the well know RGD peptide sequence that acts as a fibronectin receptor. There are well known peptide fragments of the parathyroid hormone, e.g., the 1-34 PTH fragment, that have biological activity on the skeleton. Other examples of biologically active synthetic peptide fragments based on sequences from the biomolecules Angiotensin I and II are described in U.S. Pat. No. 6,916,783. These biologically active peptides may also be used in these pliable medical devices.

ABM is the “osteoconductive component” of the pliable medical device. An osteoconductive material is one that promotes bone deposition, provided that fully differentiated and competent osteogenic cells are available at the site of implantation. In addition to anorganic bone mineral matrix (ABM), the osteoconductive component may also be a synthetic alloplast matrix or some other type of xenograft or allograft mineralized matrix that might not fit the definition of “anorganic.” The alloplast could be a calcium phosphate material or it could be one of several other inorganic materials that have been used previously in bone graft substitute formulations, e.g., calcium carbonates, calcium sulphates, calcium silicates, or mixtures thereof that could function as biocompatible, osteoconductive matrices. The anorganic bone mineral matrix, synthetic alloplast matrix, and xenograft or allograft mineralized matrix are collectively referred to as the osteoconductive component.

The P-15 material mentioned previously is structurally identical to a fifteen amino acid sequence that is found in natural Type I collagen, but is made synthetically. The P-15 used is not osteoinductive (having the ability to induce de novo differentiation of competent osteogenic cells from nonosteogenic and uncommitted cells). The P-15 will not take non-bone cells and make bone cells out of them, but instead, P-15 is able to recruit cells that are already destined to become bone cells (osteogenic) and cause them to lay down on the surface of the matrix and start making bone. This is advantageous in the event that the pliable medical device migrates away from the osteogenic site, i.e., a site predisposed to growing bone cells. In such an event, no bone cells will grow at the site of migration, whereas, an osteoinductive material, typical of the prior art products, could cause ectopic bone to grow wherever the material happened to migrate, which could be very detrimental and problematic for the patient. The pliable medical device needs to be in physical contact with an osteogenic site in order for bone to grow. Thus, in a spine fusion application, a cylinder of the pliable medical device positioned at each end, adjacent to different vertebra, will allow bone to grow from each end, and meet in the middle, forming a new bone structure that was not there before.

The P-15 coated ABM particles have a mean particle diameter of 300 microns, and nearly all will fall within a range between 250 microns to 425 microns. However, a particle size range between 50 microns to 2000 microns may also be used. The two materials, ABM and the hydrated hydrogel material, are mixed at low speed (approximately fifty rpm) for about two minutes. Next, a second 130 gram amount of ABM/P-15 particles are added and mixed for an additional seventeen minutes. A vacuum of at least twenty inches of Hg is drawn on the mixing unit and mixed for an additional five minutes. The resulting ABM/P-15/CMC hydrogel material, hereinafter referred to as “putty”, is transferred from the mixing unit and may be stored, or processed further according to the following steps.

Though the putty can be used by a physician in this form to treat bone damage, it may be further processed by a lyophilization step into several different shapes. The following examples are simply illustrative and not intended to be limiting to only the shapes described. In addition to the cylinder, cube, and sheet shapes described below, any other shapes for a particular purpose could be made, such as star shaped, toroid shaped, pyramid shaped, sphere shaped, and any number of irregularly shaped embodiments.

Example 1 Preparation of Lyophilized Cylinders

An extrusion device is fitted with a 6.5 mm diameter orifice and filled with the putty prepared as described above. Cylinders, fifty mm in length, are extruded from the device onto a chilled (−30° C.) metal plate, or any other appropriate chilled surface. The cylinders are further cooled to −55° C. on the shelves of a lyophilization vessel. Lyophilization is a means of water removal, achieved by freezing a wet substance and causing the ice to sublime directly to vapor by exposing it to a surrounding low pressure. A vacuum of 200 mTorr is applied to the frozen cylinders and maintained for eighteen hours. During that time the lyophilization chamber is allowed to warm to room temperature, approximately 25° C., or heated somewhat to speed up the sublimation process. These conditions are sufficient to reduce the water content of the cylinders to about 3%. The resulting lyophilized cylinders are dry in appearance, flexible and able to absorb blood and serous fluids. Please see FIGS. 1-3.

Lyophilization has many advantages over simply air drying or vacuum drying the putty. When the putty is allowed to air dry or vacuum dry without freezing, the hydrogel forms a skin around the ABM particles that is occlusive and prevents cells from getting to the particles. Freezing the material first, and then evaporating the water leaves many holes where the ice crystals sublime giving rise to a very porous structure. The porous structure allows cells, blood, and bone marrow easy access through the holes to the particles. With air drying and vacuum drying without freezing, the hydogel structure continues to collapse as the water evaporates, thus preventing the creation of a porous structure. Sublimation, rather than evaporation, is the key to creating the porous structure desired.

Next, the lyophilized cylinders are placed into sealed but breathable microbial barrier pouches and sterilized in a steam autoclave. The pouches may be made of paper or more typically Tyvec® from DuPont. The sterilization cycle includes a twenty minute temperature ramp-up to 121° C., temperature maintenance at 121° C. for thirty minutes, followed by a one hour cool down period to room temperature, approximately 25° C. The lyophilized cylinders are substantially unchanged in their physical handling properties following this sterilization procedure.

Because the lyophilized cylinders are easily cut into smaller pieces as shown in FIG. 2, it is easy to load those pieces directly into a osteogenic site, such as the bone defect shown in FIG. 3, or into metal spine fusion cages, such as the BAK-C cage shown in FIG. 5. This loading can be done before the cage is placed into the prepared inter-body location during an anterior cervical spine discectomy and vertebral body fusion.

Example 2 Preparation of Lyophilized Sheets

The putty prepared as described above is loaded by injection into a Delrin mold containing a channel, twenty-four mm wide by four mm deep by 150 mm in length. The sheet-like mold is fitted with a releasable top plate that is typically bolted to the bottom plate. The loaded sheet-like mold is placed into a freezing unit and the sheet-like mold and putty are cooled to −55° C. After reaching this desired temperature, the top plate of the sheet-like mold is loosened to allow water to sublime away, and the sheet-like mold, still cold, is placed into a lyophilization chamber at 135 mTorr. During the sublimation process the lyophilization chamber is allowed to gradually warm to room temperature, approximately 25° C., or heated somewhat to speed up the sublimation process. The resulting dry flexible lyophilized sheet is easily removed from the mold and cut with standard scissors (FIG. 4). The lyophilized sheet is compliant for fitting onto an irregular surface. When dampened, the sheet maintains its proximity to the applied surface very well. The lyophilized sheet could also be sterilized in a steam autoclave as described above, prior to use.

High energy tibial fractures (auto accidents) are prone to becoming non-unions. These non-unions are often repaired by debrieding the soft tissue from the non-union area and loading the open space between the fracture ends with autograft bone. To better localize the autograft bone, a lyophilized sheet would be wrapped around the tibia enclosing the non-union in a “repair burrito.” The musculature and other soft tissues would then envelope the repair site.

Example 3 Preparation of Lyophilized Cubes

The putty prepared as described above is pressed into a Delrin mold, using a stainless steel laboratory spatula, or any other suitable utensil, or by hand, to create cubes, one centimeter on edge. The mold and putty is frozen on a dry ice slab, or any suitably chilled surface or freezer shelf or with liquid nitrogen, and placed, still frozen, into a lyophilization flask. The putty is then subjected to a vacuum of 125 mTorr for forty-eight hours while warming the lyophilization chamber to room temperature, approximately 25° C. The lyophilized cubes can be sterilized in a steam autoclave, as described above, prior to use. The lyophilized cubes are dry in appearance but flexible and readily soak up blood and mix easily with bone marrow aspirate. The lyophilized cubes could be mixed with autograft bone harvested by conventional techniques from areas such as the iliac crest and serve to expand the useful volume of bone graft material available to the orthopedic surgeon.

When cancellous autograft bone is harvested from the iliac crest, a cortical bone window is cut from the top of the ilium and cancellous bone is harvested from the space between the inner and outer cortical bone tables. Lyophilized cubes (or cylinders) are easily placed into the void created by the removal of the cancellous bone graft (FIG. 3). The lyophilized cubes would facilitate the re-growth of host bone.

Lyophilized cubes or short lyophilized cylinders could be loaded into the hollow central portion of a structural allograft device such as the fibular ring allograft device shown in FIG. 6, or machined allograft dowels, before insertion of the structural device into the prepared inter-vertebral body space.

The lyophilized putty, no matter what shape, is a firm but pliable medical device that will retain its shape without a containment device as required with putty. Because the device is solid, it is easy to locate or position in-vivo and, in the moist environment of the body, it will hold its shape well and for an extended period of time. Because the lyophilized putty is porous, it adsorbs blood and other beneficial cell containing body fluids, such as bone marrow aspirate, contributing to its superior bone repair efficacy in comparison to the analogous putty. In addition these lyophilized putty devices are easier to terminally steam sterilize than the analogous putty because there is virtually no moisture present to boil and “blow-out” of the containment device (syringe). The glycerin or other fluid material that is present in the formulation lends pliability but has a low vapor pressure.

NaCMC is a key component of the hydrogel utilized in making the lyophilized putty. It is stable to the relatively high pH of the product. NaCMC is stable to steam sterilization and doesn't interfere with the biological action of the product. Other polysaccharide hydrogels such as hyaluronic acid, hydroxyethyl cellulose (HEC), hydroxypropyl methylcellulose (HPC), methylcellulose (MC); and ethylcellulose (EC) may be suitable substitutes for NaCMC. Furthermore, some synthetic polymers, such as polyvinvylalcohol and polyvinylpyrrolidone may be suitable substitutes for NaCMC. Some hydrogel materials, such as hyaluronic acid and chitosan, may not be satisfactory for steam sterilization, which will cause these materials to degrade, losing viscosity and the ability to suspend particles. For such materials, alternative sterilization methods must be employed.

In one aspect, the invention features a composition of matter suitable for repairing bone damage and promoting bone formation in mammals including: (i) from 5% to 20% (w/w) of a dispersing agent selected from glycerin, polyethylene glycol, N-methyl pyrrolidone, and triacetin; (ii) from 1.0% to 6.0% (w/w) of a polymer selected from sodium carboxymethylcellulose, hyaluronic acid, polyvinylalcohol, polyvinylpyrrolidone, hydroxyethyl cellulose, hydroxypropyl methylcellulose, methylcellulose, and ethylcellulose; (iii) from 65% to 90% (w/w) of an osteoconductive component; and (iv) from 1% to 5% (w/w) water, wherein the composition is porous and pliable. The dispersing agent can be 5% to 15%, 8% to 15%, 8% to 20%, 10% to 20%, 14% to 20%, 5% to 12%, or about 8%, 9%, 10%, 11%, 12%, 13%, 14%, or 15% (w/w) of the composition of the invention. The polymer can be 1.5% to 3.0%, 1.0% to 5.0%, 1.0% to 4.0%, 2.0% to 5.0%, or about 1.0%, 1.5%, 2.0%, 2.5%, 3.0%, 3.5%, or 4% (w/w) of the composition of the invention. The osteoconductive component can be 70% to 90%, 75% to 90%, 80% to 90%, 82% to 90%, or about 83%, 84%, 85%, 86%, 87%, 88%, 89%, or 90% (w/w) of the composition of the invention. Water can be 1.5% to 5%, 2% to 4%, 2.5% to 5%, 1% to 3%, or about 1.5%, 2%, 2.5%, 3%, 3.5%, 4%, 4.5%, or 5% (w/w) of the composition of the invention. In certain embodiments, the dispersing agent selected is glycerin; the polymer is carboxymethylcellulose; and the osteoconductive component is anorganic bone mineral matrix. In one particular embodiment, the composition includes: (i) from 8% to 15% (w/w) glycerin; (ii) from 1.5% to 3.0% (w/w) sodium carboxymethylcellulose; (iii) from 82% to 90% (w/w) anorganic bone mineral matrix; and (iv) from 2% to 4% (w/w) water.

As used herein, the term “porosity” refers to the fraction of void volume (expressed herein as a percentage) in the compositions of the invention. The compositions of the invention typically have a porosity in the range of 10% to 35%. Depending upon the ratios of the components used, the porosity may be from 5% to 30%, 5% to 25%, 5% to 20%, 5% to 15%, 10% to 25%, 15% to 25%, or 10% to 20%.

As used herein, the term “pliable” refers to the ability of the compositions of the invention to bend freely without breaking when shaped as best shown in FIGS. 1 and 4. To demonstrate pliability, a cut strip of lyophilized material prepared as described above in Example 2 has dimensions of 10 mm wide by 30 mm long by 2 mm thick. This cut strip was clamped in a spring holder in a horizontal position at 10 mm of length leaving 20 mm of length extended. A one gram weight was placed on the free end of the strip for twenty seconds and the amount of deflection below the horizontal was measured. The cut strip was then removed from the clamp and placed on a flat surface until it lay flat on the surface. The cut strip was then clamped as before, the one gram weight placed on the free end, and the deflection measured after 20 seconds. This procedure was repeated a third time. The three tests had measured deflections of the free end below the horizontal of 5.5 mm, 6.0 mm, and 6.0 mm with a measured accuracy of approximately +/−0.5 mm. For all three tests, the cut strip curved fairly uniformly and did not break. It was also observed that after removing the weight and while still clamped, the cut strip recovered a good deal of its “straightness” with only approximately a 2 mm deflection below the horizontal measured at the free end of the cut strip. It is anticipated that the lyophilized formulation, without the dispersing agent, will be less pliable but is otherwise identical in composition.

Having described the present invention, it will be understood by those skilled in the art that many changes in construction and widely differing embodiments and applications of the invention will suggest themselves without departing from the scope of the present invention. 

1-61. (canceled)
 62. A pliable implantable composition comprising (i) a dispersing agent selected from glycerin, polyethylene glycol, N-methyl pyrrolidone, and triacetin; (ii) a polymer selected from sodium carboxymethylcellulose, hyaluronic acid, polyvinylalcohol, polyvinylpyrrolidone, hydroxyethyl cellulose, hydroxypropyl methylcellulose, methylcellulose, and ethylcellulose; and (iii) an osteoconductive component, wherein said pliable implantable composition has a porosity of from 10 to 35%.
 63. The pliable implantable composition of claim 62, wherein said dispersing agent is glycerin.
 64. The pliable implantable composition of claim 62, wherein said polymer is sodium carboxymethylcellulose.
 65. The pliable implantable composition of claim 62, wherein said polymer is sodium carboxymethylcellulose and said dispersing agent is glycerin.
 66. The pliable implantable composition of claim 62, wherein said osteoconductive component comprises a calcium phosphate material and a biologically active peptide.
 67. The pliable implantable composition of claim 66, wherein said biologically active peptide is selected from P-15, chrysalin, alpha1(I)-CB3, an RGD peptide, a PTH peptide, and a cytomodulin protein.
 68. The pliable implantable composition of claim 67, wherein said osteoconductive component is comprised of particles having diameters between 50 microns to 2,000 microns.
 69. The pliable implantable composition of claim 68, wherein said osteoconductive component is comprised of particles having diameters between 250 microns to 425 microns.
 70. The pliable implantable composition of claim 69, wherein said osteoconductive component is anorganic bone mineral and said biologically active peptide is P-15.
 71. The pliable implantable composition of claim 62, wherein said pliable implantable composition is in the form of a cylinder, a cube, a sheet, a star, a toroid, a pyramid, a sphere, or an irregular shape.
 72. The pliable implantable composition of claim 71, wherein said pliable implantable composition is in the shape of a cylinder.
 73. The pliable implantable composition of claim 71, wherein said pliable implantable composition is in the shape of a cube.
 74. The pliable implantable composition of claim 71, wherein said pliable implantable composition is in the shape of a sheet.
 75. The pliable implantable composition of claim 62, wherein said pliable implantable composition is produced by: (a) preparing a quantity of a hydrogel material by mixing (i) a quantity of polymer selected from sodium carboxymethylcellulose, hyaluronic acid, polyvinylalcohol, polyvinylpyrrolidone, hydroxyethyl cellulose, hydroxypropyl methylcellulose, methylcellulose, and ethylcellulose with (ii) a quantity of a dispersing agent selected from glycerin, polyethylene glycol, N-methyl pyrrolidone, and triacetin, and (iii) a quantity of water; (b) mixing said hydrogel material with a quantity of an osteoconductive component to form a putty; and (c) lyophilizing said putty to form said pliable implantable composition, wherein prior to step (c) said hydrogel material or said putty is placed under a vacuum.
 76. A pliable implantable composition comprising: (i) from 5% to 20% (w/w) of a dispersing agent selected from glycerin, polyethylene glycol, N-methyl pyrrolidone, and triacetin; (ii) from 1.0% to 6.0% (w/w) of a polymer selected from sodium carboxymethylcellulose, hyaluronic acid, polyvinylalcohol, polyvinylpyrrolidone, hydroxyethyl cellulose, hydroxypropyl methylcellulose, methylcellulose, and ethylcellulose; (iii) from 65% to 90% (w/w) of an osteoconductive component; and (iv) from 1% to 5% (w/w) water, wherein said pliable implantable composition has a porosity of from 5 to 30%.
 77. The pliable implantable composition of claim 76, wherein said composition has a porosity of 10% to 25%.
 78. The pliable implantable composition of claim 76, wherein said dispersing agent is glycerin; said polymer is carboxymethylcellulose; and said osteoconductive component is anorganic bone mineral.
 79. The pliable implantable composition of claim 78, wherein said composition comprises: (i) from 8% to 15% (w/w) glycerin; (ii) from 1.5% to 3.0% (w/w) sodium carboxymethylcellulose; (iii) from 82% to 90% (w/w) anorganic bone mineral; and (iv) from 2.5% to 5% (w/w) water.
 80. A method for implanting a pliable implantable composition of any of the above claims into a subject, said method comprising inserting said pliable implantable composition at an osteogenic site.
 81. The method of claim 80, further comprising (a) positioning a first end of said pliable implantable composition at a first osteogenic site; and (b) positioning a second end of said pliable implantable composition at a second osteogenic site, wherein said pliable implantable composition promotes bone formation across said first and second ends of said pliable implantable composition to form a new bone structure between said first and second osteogenic sites.
 82. The method of claim 81, wherein said first osteogenic site is a portion of a first vertebra and said second osteogenic site is a portion of a second vertebra.
 83. The method according to claim 80, further comprising (a) loading an open space of a non-union area between two fracture ends of a bone with autograft bone; and (b) wrapping a sheet of said pliable implantable composition around said non-union area. 